CN112494016A

CN112494016A - Method for tracking cardiac cycle events using blood pressure

Info

Publication number: CN112494016A
Application number: CN201911416527.1A
Authority: CN
Inventors: 李连波; 郑欲晓
Original assignee: Insight Lifetech Co Ltd
Current assignee: Insight Lifetech Co Ltd
Priority date: 2019-12-31
Filing date: 2019-12-31
Publication date: 2021-03-16
Anticipated expiration: 2039-12-31
Also published as: CN112494016B

Abstract

The present disclosure relates to a method of tracking cardiac cycle events using blood pressure, comprising: the method comprises the steps of simultaneously measuring pressures close to a near-end side in a blood vessel and far from the near-end side in the blood vessel for multiple times in any cardiac cycle, generating a first initial pressure signal and a second initial pressure signal, calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio, sequentially selecting a preset number of pressure ratios from the initial pressure ratios from small to large, and calculating the average value of the preset number of pressure ratios according to the selected preset number of pressure ratios.

Description

Method for tracking cardiac cycle events using blood pressure

Technical Field

The present disclosure relates specifically to a method of tracking cardiac cycle events using blood pressure.

Background

Coronary artery disease is one of the leading causes of death worldwide, and the ability to better diagnose, monitor and treat coronary artery disease can save lives. Coronary angiography is a technique conventionally used to evaluate stenosis of coronary arteries, but it does not reflect the actual function of coronary vessels, and therefore it is basically impossible to determine whether a stenosed coronary artery is associated with myocardial ischemia in a patient. At present, the method for clinically judging stenosis of coronary artery mainly applies the technique of Fractional Flow Reserve (FFR) obtained by pressure guide wire examination.

However, the following drawbacks exist in obtaining FFR: the need to inject a hyperemic inducing drug (e.g., adenosine triphosphate, ATP) into the coronary arteries prior to FFR measurement to maximize hyperemia in the coronary arteries increases the clinical procedure time, causes discomfort to the patient, greatly increases the medical costs, and may also trigger allergic reactions in the patient.

Disclosure of Invention

The present disclosure has been made in view of the above circumstances, and an object thereof is to provide a method capable of tracking a cardiac cycle event without injecting a congestion-inducing drug and using blood pressure more safely and efficiently.

To this end, a first aspect of the present disclosure provides a method for tracking cardiac cycle events using blood pressure, comprising: measuring the pressure in the blood vessel close to the near end side at a certain sampling rate in any cardiac cycle and generating a first initial pressure signal, and measuring the pressure in the blood vessel far from the near end side at a certain sampling rate and generating a second initial pressure signal; according to the first initial pressure signal and the second initial pressure signal, calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal to obtain an initial pressure ratio, sequentially selecting a preset number of pressure ratios from the initial pressure ratios from small to large, and calculating the average value of the preset number of pressure ratios according to the selected preset number of pressure ratios.

In the present disclosure, the pressure in the proximal side of the blood vessel and the pressure in the distal side of the blood vessel are measured simultaneously a plurality of times during any one cardiac cycle and first and second initial pressure signals are generated. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. And sequentially selecting a preset number of pressure ratios from the initial pressure ratios in a descending order, and calculating the average value of the preset number of pressure ratios according to the selected preset number of pressure ratios. Thereby, a method of tracking cardiac circulatory events using blood pressure without the need for injection of congestion-inducing drugs can be provided.

In the intravascular pressure measurement system according to the first aspect of the present disclosure, the cardiac cycle optionally includes a whole cycle of diastole and systole. Thereby, the blood pressure of the blood vessel in the diastolic and systolic periods can be obtained.

A second aspect of the present disclosure provides a method for tracking cardiac cycle events using blood pressure, comprising: measuring the pressure in the blood vessel close to the proximal side at a certain sampling rate and generating a first initial pressure signal, and measuring the pressure in the blood vessel far from the proximal side at a certain sampling rate and generating a second initial pressure signal in any one cardiac cycle, wherein the cardiac cycle comprises the diastole period of diastole and the systole period of systole; according to the first initial pressure signal and the second initial pressure signal, calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal to obtain an initial pressure ratio, obtaining the pressure ratio in the diastolic period of the cardiac cycle from the initial pressure ratio, and selecting the minimum pressure ratio from the pressure ratios.

In the present disclosure, the pressure in the proximal side of the blood vessel and the pressure in the distal side of the blood vessel are measured simultaneously a plurality of times during any one cardiac cycle and first and second initial pressure signals are generated. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. The pressure ratio values within the diastolic phase of the cardiac cycle are obtained from the initial pressure ratio values, and the smallest pressure ratio value is selected from the pressure ratio values. Thereby, a method of tracking cardiac circulatory events using blood pressure without the need for injection of congestion-inducing drugs can be provided.

A third aspect of the present disclosure provides a method for tracking cardiac cycle events using blood pressure, comprising: measuring the pressure in the blood vessel close to the near end side at a certain sampling rate in any cardiac cycle and generating a first initial pressure signal, and measuring the pressure in the blood vessel far from the near end side at a certain sampling rate and generating a second initial pressure signal; according to the first initial pressure signal and the second initial pressure signal, calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal to obtain an initial pressure ratio, obtaining the pressure ratio in a first preset period of the cardiac cycle from the initial pressure ratio, and selecting the minimum pressure ratio from the pressure ratios, wherein the average value of the pressure values of the first initial pressure signal is obtained according to the first initial pressure signal, and a first intersection point is obtained according to the first initial pressure signal and the average value, and the first preset period is a period from the first intersection point to the minimum value of the first initial pressure signal and the first initial pressure signal is in continuous descending.

In the present disclosure, the pressure in the proximal side of the blood vessel and the pressure in the distal side of the blood vessel are measured simultaneously a plurality of times during any one cardiac cycle and first and second initial pressure signals are generated. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. Pressure ratios within a first predetermined period of the cardiac cycle are obtained from the initial pressure ratios and the smallest pressure ratio is selected from the pressure ratios. Thereby, a method of tracking cardiac circulatory events using blood pressure without the need for injection of congestion-inducing drugs can be provided.

A fourth aspect of the present disclosure provides a method for tracking cardiac cycle events using blood pressure, comprising: measuring the pressure in the blood vessel close to the near end side at a certain sampling rate in any cardiac cycle and generating a first initial pressure signal, and measuring the pressure in the blood vessel far from the near end side at a certain sampling rate and generating a second initial pressure signal; according to the first initial pressure signal and the second initial pressure signal, calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal to obtain an initial pressure ratio, obtaining the pressure ratio in a second preset period of the cardiac cycle from the initial pressure ratio, and selecting the pressure ratio corresponding to the midpoint moment of the second preset period from the pressure ratios, wherein the average value of the pressure values of the first initial pressure signal is obtained according to the first initial pressure signal, and a first intersection point is obtained according to the first initial pressure signal and the average value, and the second preset period is the period from the first intersection point to the minimum value of the first initial pressure signal.

In the present disclosure, the pressure in the proximal side of the blood vessel and the pressure in the distal side of the blood vessel are measured simultaneously a plurality of times during any one cardiac cycle and first and second initial pressure signals are generated. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. A pressure ratio value within a second predetermined period of the cardiac cycle is obtained from the initial pressure ratio values, and a pressure ratio value corresponding to a midpoint time of the second predetermined period is selected from the pressure ratio values. Thereby, a method of tracking cardiac circulatory events using blood pressure without the need for injection of congestion-inducing drugs can be provided.

A fifth aspect of the present disclosure provides a method for tracking cardiac cycle events using blood pressure, comprising: measuring the pressure in the blood vessel close to the near end side at a certain sampling rate in any cardiac cycle and generating a first initial pressure signal, and measuring the pressure in the blood vessel far from the near end side at a certain sampling rate and generating a second initial pressure signal; according to the first initial pressure signal and the second initial pressure signal, calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal to obtain an initial pressure ratio, obtaining a pressure ratio in a third preset period of the cardiac cycle from the initial pressure ratio, and calculating the average value of the pressure ratios, wherein the average value of the pressure values of the first initial pressure signal is obtained according to the first initial pressure signal, and a first intersection point is obtained according to the first initial pressure signal and the average value, and the third preset period is a period from the first intersection point to 80% of the cardiac cycle.

In the present disclosure, the pressure in the proximal side of the blood vessel and the pressure in the distal side of the blood vessel are measured simultaneously a plurality of times during any one cardiac cycle and first and second initial pressure signals are generated. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. A pressure ratio value within a third predetermined period of the cardiac cycle is obtained from the initial pressure ratio values and an average of the pressure ratio values is calculated. Thereby, a method of tracking cardiac circulatory events using blood pressure without the need for injection of congestion-inducing drugs can be provided.

A sixth aspect of the present disclosure provides a method for tracking cardiac cycle events using blood pressure, comprising: measuring the pressure in the blood vessel close to the near end side at a certain sampling rate in any cardiac cycle and generating a first initial pressure signal, and measuring the pressure in the blood vessel far from the near end side at a certain sampling rate and generating a second initial pressure signal; according to the first initial pressure signal and the second initial pressure signal, calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal to obtain an initial pressure ratio, obtaining a pressure ratio in a second preset period of the cardiac cycle from the initial pressure ratio, and calculating the average value of the pressure ratios, wherein the average value of the pressure values of the first initial pressure signal is obtained according to the first initial pressure signal, and a first intersection point is obtained according to the first initial pressure signal and the average value, and the second preset period is the period from the first intersection point to the minimum value of the first initial pressure signal.

In the present disclosure, the pressure in the proximal side of the blood vessel and the pressure in the distal side of the blood vessel are measured simultaneously a plurality of times during any one cardiac cycle and first and second initial pressure signals are generated. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. Pressure ratios within a second predetermined period of the cardiac cycle are obtained from the initial pressure ratios and an average of the pressure ratios is calculated. Thereby, a method of tracking cardiac circulatory events using blood pressure without the need for injection of congestion-inducing drugs can be provided.

A seventh aspect of the present disclosure provides a method for tracking cardiac cycle events using blood pressure, comprising: measuring the pressure in the blood vessel close to the near end side at a certain sampling rate in any cardiac cycle and generating a first initial pressure signal, and measuring the pressure in the blood vessel far from the near end side at a certain sampling rate and generating a second initial pressure signal; according to the first initial pressure signal and the second initial pressure signal, calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal to obtain an initial pressure ratio, obtaining the pressure ratio in a fourth preset period of the cardiac cycle from the initial pressure ratio, and selecting the pressure ratio corresponding to the midpoint moment of the fourth preset period from the pressure ratios, wherein a derivative of the second initial pressure signal relative to time is obtained according to the second initial pressure signal, a first midpoint moment and a second midpoint moment are obtained according to the second initial pressure signal and the derivative, and the fourth preset period is a period from the first midpoint moment to the second midpoint moment.

In the present disclosure, the pressure in the proximal side of the blood vessel and the pressure in the distal side of the blood vessel are measured simultaneously a plurality of times during any one cardiac cycle and first and second initial pressure signals are generated. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. And obtaining the pressure ratio value in a fourth preset period of the cardiac cycle from the initial pressure ratio value, and selecting the pressure ratio value corresponding to the midpoint moment of the fourth preset period from the pressure ratio values. Thereby, a method of tracking cardiac circulatory events using blood pressure without the need for injection of congestion-inducing drugs can be provided.

An eighth aspect of the present disclosure provides a method for tracking cardiac cycle events using blood pressure, comprising: measuring the pressure in the blood vessel close to the near end side at a certain sampling rate in any cardiac cycle and generating a first initial pressure signal, and measuring the pressure in the blood vessel far from the near end side at a certain sampling rate and generating a second initial pressure signal; calculating a ratio of a pressure value of the second initial pressure signal to a pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio, obtaining a pressure ratio in a fifth preset period of the cardiac cycle from the initial pressure ratio, and calculating an average value of the pressure ratios, wherein the fifth preset period is a period from a first occurrence time to a last occurrence time of a derivative value of the second pressure signal with respect to time in the fourth preset period, a derivative of the second initial pressure signal with respect to time is obtained according to the second initial pressure signal, and a first midpoint time and a second midpoint time are obtained according to the second initial pressure signal and the derivative, the fourth preset period is a period from the first midpoint time to the second midpoint time.

In the present disclosure, the pressure in the proximal side of the blood vessel and the pressure in the distal side of the blood vessel are measured simultaneously a plurality of times during any one cardiac cycle and first and second initial pressure signals are generated. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. A pressure ratio value within a fifth preset period of the cardiac cycle is obtained from the initial pressure ratio values, and an average of the pressure ratio values is calculated. Thereby, a method of tracking cardiac circulatory events using blood pressure without the need for injection of congestion-inducing drugs can be provided.

According to the present invention, it is possible to provide a method for tracking cardiac circulatory events using blood pressure without the need for injection of congestion-inducing drugs, and with greater safety and efficiency.

Drawings

Fig. 1 is a schematic structural view showing an intravascular pressure measurement system according to an example of the present disclosure.

Fig. 2 is a schematic diagram illustrating an intravascular pressure measurement system according to an example of the present disclosure.

Fig. 3 is a schematic view of an interventional body showing an intravascular pressure measurement system according to an example of the present disclosure.

Fig. 4 is a sectional view showing an intravascular pressure measurement system according to an example of the present disclosure applied to a coronary artery.

Fig. 5 is a pressure waveform diagram illustrating a plurality of cardiac cycles in accordance with an example of the present disclosure.

Fig. 6 is a pressure waveform diagram illustrating one cardiac cycle of fig. 5 in accordance with an example of the present disclosure.

Fig. 7 is a pressure waveform diagram illustrating one cardiac cycle of fig. 5 according to another example of the present disclosure.

The reference numbers illustrate:

1 … system, 10 … blood pressure measurement device, 20 … withdrawal device, 30 … host, 100 … guide catheter, 100a … proximal side, 100b … distal side, 101 … internal lumen, 102 … first pressure sensor, 110 … blood pressure measurement catheter, 110a … proximal side, 110b … distal side, 111 … internal lumen, 112 … second pressure sensor, 113 … signal path, 201 … drive module, 202 … switch module, 203 … signal reception module, 300 … image processing device, 310 … blood pressure processing device, 400 … coronary artery, 401 … proximal coronary artery, 402 … distal coronary artery, 403 … stenotic lesion.

Detailed Description

Hereinafter, preferred embodiments of the present disclosure will be described in detail with reference to the accompanying drawings. In the following description, the same components are denoted by the same reference numerals, and redundant description thereof is omitted. The drawings are schematic and the ratio of the dimensions of the components and the shapes of the components may be different from the actual ones.

In addition, the headings and the like referred to in the following description of the present disclosure are not intended to limit the content or scope of the present disclosure, but merely serve as a reminder for reading. Such a subtitle should neither be understood as a content for segmenting an article, nor should the content under the subtitle be limited to only the scope of the subtitle.

The present disclosure provides a method for tracking cardiac cycle events using blood pressure, in which blood pressure can be used more safely and efficiently without the need for injection of a congestion-inducing drug, for example, a lesion condition of a blood vessel of a patient can be judged without the need for injection of a congestion-inducing drug.

Fig. 1 is a schematic structural view showing an intravascular pressure measurement system 1 according to an example of the present disclosure. Fig. 2 is a schematic diagram showing an intravascular pressure measurement system 1 according to an example of the present disclosure. Fig. 3 is a schematic view showing an interventional human body of an intravascular pressure measurement system 1 according to an example of the present disclosure. Fig. 4 is a sectional view showing an intravascular pressure measurement system 1 according to an example of the present disclosure applied to a coronary artery 400.

In some examples, as shown in fig. 1-3, an intravascular pressure measurement system 1 (simply "system 1") can include a blood pressure measurement device 10, an evacuation device 20, and a host 30. The blood pressure measuring device 10 may be connected to an evacuation device 20, and the evacuation device 20 may be connected to a host computer 30. The blood pressure measurement device 10 may measure the blood pressure of the blood vessel (also referred to as "intravascular pressure", simply "blood pressure" and "pressure") within the blood vessel and transmit it to the retraction device 20. The retraction device 20 may receive a signal (also referred to as a "pressure signal") including the blood pressure of the blood vessel in the blood vessel from the blood pressure measurement device 10, and may transmit the pressure signal to the host 30 for processing.

In some examples, as shown in fig. 1 and 2, a side close to a host 30 (described later) may be a proximal side 30a and a side far from the host 30 may be a distal side 30 b.

The intravascular pressure measurement system 1 according to the present disclosure can measure intravascular blood pressure (also referred to as "intravascular pressure") using an interventional catheter technique to determine a lesion 403 (see fig. 4) in a blood vessel of a patient, for example, a stenosis. The intravascular pressure measurement system 1 can be used to measure and process the pressure in the blood vessel of the patient (for example, to obtain a first target ratio and/or a second target ratio described later), can determine the pathological condition of the blood vessel of the patient without injecting a congestion-inducing drug, and can more specifically determine the size of the stent implantation site.

In some examples, a method of using blood pressure to track cardiac cycle events may include measuring intravascular proximal side 30a pressure at a sampling rate and generating a first initial pressure signal and measuring intravascular distal side 30b pressure at a sampling rate and generating a second initial pressure signal (described in detail later) during any one cardiac cycle.

In some examples, the cardiac cycle may include the entire cycle of diastolic phases of diastole and systolic phases of systole. Thereby, the blood pressure of the blood vessel in the diastolic and systolic periods can be obtained.

In some examples, the blood pressure measurement device 10 may measure pressure within the blood vessel proximate the proximal side 30a and generate a pressure signal, and the blood pressure measurement device 10 may measure pressure within the blood vessel distal the proximal side 30a and generate a pressure signal. For example, the blood pressure measurement device 10 may include a proximal pressure measurement device (described later) that may be used to measure pressure within the blood vessel proximate the proximal side 30a and generate a pressure signal. The blood pressure measurement device 10 may include a distal pressure measurement device (described later) that may be used to measure pressure within the blood vessel proximate the proximal side 30a and generate a pressure signal.

In some examples, as shown in fig. 1, the proximal pressure measurement device may be a guide catheter 100 (described later) for measuring pressure within the blood vessel near the proximal side 30a and generating a pressure signal. Examples of the present disclosure are not limited thereto and the proximal pressure measuring device may be other devices to obtain the pressure within the blood vessel near the proximal side 30 a.

In some examples, as shown in fig. 1, the guide catheter 100 may be in the form of an elongated tube, and the guide catheter 100 may have an internal lumen 101. In some examples, the guiding catheter 100 has a proximal side 100a that is proximal to the host 30 (described later) and a distal side 100b that is distal to the host 30.

In some examples, the guide catheter 100 is provided with a first pressure sensor 102.

In some examples, the first pressure sensor 102 may be an invasive blood pressure sensor that may be directly connected to a port on the proximal side 100a of the guiding catheter 100 so as to be disposed on the guiding catheter 100. For example, the first pressure sensor 102 may be provided with a circular port that mates with the tubular structure of the guiding catheter 100 for connection to the guiding catheter 100. This allows better matching of the guiding catheter 100 and the first pressure sensor 102, and better measurement of the intravascular pressure.

In some examples, first pressure sensor 102 may sense the pressure resulting from the flow of liquid from distal side 100b into internal cavity 101 of guide catheter 100. In some examples, in operation of the system 1, the guiding catheter 100 may acquire a first initial pressure signal (e.g., a first pressure signal and a third pressure signal, described later) within the blood vessel proximate the proximal side 30a (relative to a second pressure sensor 112, described later) at a sampling rate via the first pressure sensor 102.

In some examples, the guiding catheter 100 may generate a first initial pressure signal by the first pressure sensor 102 acquiring a pressure within the blood vessel proximate the proximal side 30a at a first sampling rate. For example, the guiding catheter 100 may be placed in a blood vessel of the human body and a port of the distal side 100b of the guiding catheter 100 is placed in the blood vessel at a position close to the proximal side 30a (also referred to as "first position", e.g. the proximal coronary artery 401 in fig. 4), the first pressure sensor 102 may be placed outside the body and connected to a port of the proximal side 100a of the guiding catheter 100, blood at the first position in the blood vessel may flow into the guiding catheter 100 and may flow from the distal side 100b of the guiding catheter 100 to the proximal side 100a of the guiding catheter 100 to be sensed by the first pressure sensor 102, whereby the first pressure sensor 102 is able to obtain the pressure in the inner cavity 101 of the guiding catheter 100, i.e. the pressure in the blood vessel at a position close to the proximal side 30a (first position), and generate a first initial pressure signal. For example, the guiding catheter 100 may acquire a cardiac-cycle-dependent pressure proximate the proximal side 30a within the blood vessel at a first sampling rate via the first pressure sensor 102 and generate a first pressure signal.

In other examples, the first pressure sensor 102 may be a capacitive pressure sensor, a resistive pressure sensor, a fiber optic pressure sensor, etc., and the first pressure sensor 102 may be disposed on the distal side 100b of the guide catheter 100, e.g., the first pressure sensor 102 may be disposed on an outer wall of the guide catheter 100. In operation of the system 1, the guide catheter 100 may be positioned within a blood vessel of the human body and the first pressure sensor 102 may be positioned within the blood vessel proximate the proximal side 30 a. In this case, the first pressure sensor 102 may directly sense a pressure within the blood vessel at a location (first location) proximate the proximal side 30a and generate a first initial pressure signal.

In some examples, the proximal pressure measuring device may be coupled to the retraction device 20, e.g., the guide catheter 100 may be coupled to the retraction device 20, and the first pressure sensor 102 may be coupled to the retraction device 20 via a transmission wire. In this case, a first initial pressure signal (e.g., a first pressure signal and a third pressure signal described later) obtained by measurement by the first pressure sensor 102 is transmitted to the retracting device 20 via the transmission wire.

In some examples, if the proximal pressure measurement device is a guide catheter 100, the diameter of the internal cavity 101 of the guide catheter 100 may be larger than the outer diameter of the distal pressure measurement device (described later). In some examples, the distal pressure measurement device may enter the internal cavity 101 from the proximal side 100a of the guide catheter 100 (see fig. 1 and 3). In this case, a blood pressure measuring catheter 110 (described later) can be disposed within the internal cavity 101 when the system 1 is in operation.

In some examples, the blood pressure measurement device 10 may include a distal pressure measurement device. In some examples, as shown in fig. 1, the distal pressure measurement device may be a blood pressure measurement catheter 110 (described later), but examples of the present disclosure are not limited thereto, and the distal pressure measurement device may also be other devices for measuring pressure within a blood vessel away from the proximal side 30a, for example, a medical guidewire with a pressure sensor.

In some examples, as shown in fig. 1 and 2, the blood pressure measurement catheter 110 can be in the form of an elongated tube, and the outer diameter of the blood pressure measurement catheter 110 can be smaller than the inner diameter of the guide catheter 100, that is, the outer diameter of the blood pressure measurement catheter 110 is smaller than the inner lumen 101. This enables the blood pressure measuring catheter 110 to be arranged better inside the guiding catheter 100 and facilitates the movement of the blood pressure measuring catheter 110 relative to the guiding catheter 100, which guiding catheter 100 can be kept still.

In some examples, as shown in fig. 1 and 2, the blood pressure measurement catheter 110 may have a proximal side 110a proximal to the host computer 30 and a distal side 110b distal to the host computer 30, the blood pressure measurement catheter 110 may have an internal cavity 111. In some examples, as shown in fig. 1, the blood pressure measurement catheter 110 may be provided with a second pressure sensor 112, and the second pressure sensor 112 may be provided on the distal end side 110b of the blood pressure measurement catheter 110. In some examples, the second pressure sensor 112 may be disposed on an outer wall of the blood pressure measurement catheter 110, and in some examples, the second pressure sensor 112 may also be disposed within the internal cavity 111 of the blood pressure measurement catheter 110, the internal cavity 111 may have a window with the second pressure sensor 112. In this case, the second pressure sensor 112 can be caused to measure the pressure in the blood vessel to generate pressure signals (e.g., a second pressure signal and a fourth pressure signal described later) when the system 1 is in operation.

In some examples, the blood pressure measurement catheter 110 may be guided along the guide catheter 100 to a preset position (also referred to as a "second position"), i.e., a position within the blood vessel distal to the distal side 30b relative to the first pressure sensor 102 (e.g., the distal coronary artery 402 in fig. 4). Specifically, during the interventional procedure, an operator, such as a medical staff member, first advances the guide catheter 100 from a certain location (e.g., femoral artery in fig. 3) on the patient (or patient) along the blood vessel to a first intravascular position, for example, as shown in fig. 3, the port of the distal end side 100b of the guide catheter 100 is placed at the first intravascular position, and then, a medical guidewire (not shown) is further advanced along the guide catheter 100 to a deep position, such as a preset position, of the blood vessel by contrast, for example, with a contrast agent. In this case, the blood pressure measuring catheter 110 is moved along the medical guide wire and by manipulating (e.g. pushing and/or pulling) the proximal side 110a of the blood pressure measuring catheter 110 outside the patient until the blood pressure measuring catheter 110 is guided to the preset position, i.e. the second pressure sensor 112 is guided to the preset position, whereby the second pressure sensor 112 is able to measure the pressure at the predetermined position within the blood vessel.

In some examples, as shown in fig. 3 and 4, in operation of the system 1, the blood pressure measuring catheter 110 may be disposed within the internal lumen 101 of the guide catheter 100 and the blood pressure measuring catheter 110 may be moved relative to the guide catheter 100, for example, by advancing the blood pressure measuring catheter 110 along the medical guidewire to a depth of a blood vessel within the patient's body by pushing on the proximal side 110a or a device connected to the proximal side 110a to enable the second pressure sensor 112 to measure a pressure at a predetermined location within the blood vessel.

In some examples, the distal side 110b of the blood pressure measuring catheter 110 may be deeper into the patient's body relative to the distal side 100b of the guiding catheter 100, i.e., the second pressure sensor 112 may generate a second initial pressure signal (e.g., a second pressure signal and a fourth pressure signal described later) relative to the first pressure sensor 102 measuring the pressure within the blood vessel further away from the proximal side 30 a.

In some examples, the first location may be a side of the coronary artery 400 proximal to the aortic port (e.g., proximal coronary artery 401) and the second location may be a side of the coronary artery 400 distal to the aortic port (e.g., distal coronary artery 402).

In some examples, a developing ring that is not transparent to X-rays may be provided on at least one side of the second pressure sensor 112. However, examples of the present disclosure are not limited thereto, and a developing ring that is not transmissive to X-rays may be provided on the distal end side 110b of the blood pressure measuring catheter 110, and the second pressure sensor 112 may be provided on the developing ring that is not transmissive to X-rays. In this case, the intravascular position of the second pressure sensor 112 can be determined.

In some examples, the blood pressure measurement catheter 110 may acquire a pressure at a preset location at a first sampling rate via the second pressure sensor 112 and generate a second pressure signal. In some examples, the blood pressure measurement catheter 110 is in a resting state while the second pressure signal is being acquired. That is, during operation of the system 1, the second pressure sensor 112 may be steered to a predetermined position, and the second pressure sensor 112 may measure a cardiac-cycle-dependent pressure at the predetermined position within the vessel at a first sampling rate and generate a second pressure signal.

In some examples, as shown in fig. 1 and 2, a blood pressure measuring catheter 110 may be coupled to the retraction device 20. The blood pressure measuring catheter 110 may be provided with a signal path 113, the signal path 113 may be disposed within the internal cavity 111 of the blood pressure measuring catheter 110, and the signal path 113 may connect the second pressure sensor 112 and the retraction device 20. In this case, a second initial pressure signal (e.g., a second pressure signal and a fourth pressure signal described later) measured by the second pressure sensor 112 is transmitted to the extracorporeal retraction device 20 via the signal path 113.

In some examples, the second pressure sensor 112 may be a capacitive pressure sensor, a resistive pressure sensor, a fiber optic pressure sensor, or the like. In addition, the second pressure sensor 112 may also be a MEMS pressure sensor. For example, the measurement range of the second pressure sensor 112 is about-50 mmHg to about +/-300 mmHg. Depending on the type of second pressure sensor 112, the signal path 113 may be a conductive medium such as an electrical wire. Further, in some embodiments, signal path 113 may also be a wireless communication link, an infrared communication link, or an ultrasonic communication link.

In the present disclosure, the blood pressure measuring catheter 110 and the guiding catheter 100 may enter or exit the patient as separate devices, respectively. In this case, the doctor can control the blood pressure measuring catheter 110 and the guide catheter 100 independently. For example, while system 1 is in operation, a healthcare worker may control blood pressure measurement catheter 110 to move relative to guide catheter 100 (e.g., to advance or retract deep into a blood vessel within a patient), and guide catheter 100 may remain stationary. By having the blood pressure measuring catheter 110 and the guide catheter 100 as separate devices, the blood pressure measuring catheter 110 can be more easily operated by the medical staff, enabling the blood pressure measuring catheter 110 to measure the pressure (e.g., the second pressure signal and a fourth pressure signal described later) within the blood vessel away from the proximal side 30 a.

In some examples, the second pressure sensor 112 may simultaneously measure the pressure within the respective corresponding vessel at the same sampling rate as the first pressure sensor 102 and generate respective corresponding pressure signals, e.g., the first pressure sensor 102 measures a first initial pressure signal while the second pressure sensor 112 measures a second initial pressure signal. In some examples, the pressure value corresponding to the first initial pressure signal ("first initial pressure value") and the pressure value corresponding to the second pressure signal (also referred to as "second initial pressure value") may correspond one-to-one.

In some examples, the first initial pressure signal and the second initial pressure signal may contain a vascular blood pressure (also referred to as "intravascular pressure") corresponding to one or more cardiac cycles (see fig. 5).

In some examples, first pressure sensor 102 and second pressure sensor 112 are in a static state. The first pressure sensor 102 measures pressure at a first location at a first sampling rate to generate a first pressure signal, while the second pressure sensor 112 measures pressure at a second location at the first sampling rate to generate a second pressure signal. In some examples, the pressure value corresponding to the first pressure signal (also referred to as the "first pressure value") and the pressure value corresponding to the second pressure signal (also referred to as the "second pressure value") may correspond one-to-one.

In some examples, the first sampling rate may range from about 30Hz to 1.5 KHz. For example, the second pressure sensor 112 may simultaneously measure the pressure within the respective corresponding blood vessels with the first pressure sensor 102 at a sampling rate of 30Hz, 50Hz, 100Hz, 200Hz, 250Hz, 300Hz, 400Hz, 500Hz, 600Hz, 700Hz, 1000Hz, 1100Hz, 1200Hz, 1300Hz, 1400Hz, 1500 Hz. Preferably, the second pressure sensor 112 and the first pressure sensor 102 may measure simultaneously at a sampling rate of 250 Hz.

In some examples, the first and second pressure signals may contain a vascular blood pressure (also referred to as "intravascular pressure") corresponding to one or more cardiac cycles (see fig. 5). In some examples, the first pressure signal and the second pressure signal include at least intravascular pressure for one complete cardiac cycle.

In some examples, the first pressure sensor 102 and the second pressure sensor 112 in the blood pressure measurement device 10 may simultaneously measure the pressure in the blood vessel and generate respective corresponding pressure signals (e.g., the first pressure signal and the second pressure signal, and perhaps the third pressure signal and the fourth pressure signal as described), and the withdrawal device 20 may be coupled to the blood pressure measurement device 10 and receive the pressure signals from the blood pressure measurement device 10.

In some examples, the blood pressure measurement device 10 may simultaneously measure pressures at a first location and a second location within a blood vessel and generate a first pressure signal and a second pressure signal.

In some examples, the retraction device 20 may be coupled to the blood pressure measurement device 10 and receive the first pressure signal and the second pressure signal, that is, the retraction device 20 may be coupled to the guide catheter 100 and receive the first pressure signal from the guide catheter 100, and the retraction device 20 may be coupled to the blood pressure measurement catheter 110 and receive the second pressure signal from the blood pressure measurement catheter 110.

In some examples, when the blood pressure measuring catheter 110 moves relative to the guide catheter 100, for example, the blood pressure measuring catheter 110 enters the blood vessel along the guide catheter 100 and is guided deep in the blood vessel, the second pressure sensor 112 may drift during the movement of the blood pressure measuring catheter 110, thereby causing an error in the measurement of the second pressure sensor 112, and the second pressure sensor 112 may be corrected and verified.

In some examples, during operation of the system 1, the pressure signals (e.g., the first initial pressure signal and the second initial pressure signal) generated by the intravascular pressure measured by the first pressure sensor 102 and the second pressure sensor 112 may be received by the retracting device 20 and then transmitted to the host 30 for processing, and the host 30 may display a time-varying pressure curve (described later) corresponding to the pressure signals.

In some examples, the second pressure sensor 112 may be placed at the first location to measure the blood pressure of the blood vessel before the second pressure sensor 112 is placed at the second location to measure the second pressure signal, i.e., the second pressure sensor 112 may measure the blood pressure of the blood vessel at the same location (e.g., the first location) as the first pressure sensor 102, thereby calibrating the second pressure sensor 112. Specifically, before the second pressure sensor 112 is guided to a predetermined position (e.g., the distal coronary artery 402), the second pressure sensor 112 may be calibrated, and the second pressure sensor 112 may be placed at a first position (e.g., the proximal coronary artery 401), in which case the second pressure sensor 112 may measure the intravascular pressure at the same position (e.g., the first position) as the first pressure sensor 102, and the second pressure sensor 112 may be calibrated with reference to the pressure signal measured by the first pressure sensor 102 until there is no significant difference between the pressure signals obtained by the second pressure sensor 112 and the first pressure sensor 102, that is, the two corresponding variation curves displayed on the host computer 30 coincide.

In some examples, after calibration of the second pressure sensor 112, the healthcare worker may obtain the second pressure signal by operating (e.g., pushing) the proximal side 110a of the blood pressure measurement catheter 110 (or a device connected to the proximal side 110a of the blood pressure measurement catheter 110) external to the patient to move the blood pressure measurement catheter 110 (e.g., to advance deep into a blood vessel within the patient) such that the second pressure sensor 112 is placed at a second location (e.g., the distal coronary artery 402). In this case, the first pressure signal obtained by the second pressure sensor 112 can be made more accurate and can be matched with the second pressure signal, which can facilitate better subsequent determination of the pathological condition of the blood vessel under test (i.e. the blood vessel measured by the first pressure sensor 102 and the second pressure sensor 112, such as the coronary artery 400 in fig. 4).

In some examples, after the second pressure sensor 112 is placed at the second location to measure and obtain the first pressure signal, the second pressure sensor 112 may be placed at the first location again to measure the blood pressure of the blood vessel, and thus the second pressure sensor 112 may be verified. Specifically, after the second pressure sensor 112 is placed in the preset position to obtain the second pressure signal, the second pressure sensor 112 may be verified, and the blood pressure measuring catheter 110 may be withdrawn by a withdrawal device 20 (described later) or manually (e.g., a medical professional may withdraw the proximal side 110a of the blood pressure measuring catheter 110), placing the second pressure sensor 112 in the first position (e.g., the proximal coronary artery 401). In this case, the second pressure sensor 112 may measure the intravascular pressure at the first location simultaneously with the first pressure sensor 102, and may verify whether the second pressure sensor 112 drifts during the movement process, i.e., whether an error occurs in the second pressure sensor 112, based on the pressure signal measured by the first pressure sensor 102. For example, if there is no significant difference between the pressure signals measured at the first position by the first pressure sensor 102 and the second pressure sensor 112, it can be determined that the pressure signal (e.g., the second pressure signal) measured by the second pressure sensor 112 can be used normally. If the pressure signals measured by the first pressure sensor 102 and the second pressure sensor 112 at the first position are significantly different, it can be determined that the pressure signal (e.g., the second pressure signal) measured by the second pressure sensor 112 cannot be used, and the accuracy of the pressure signal measured by the second pressure sensor cannot be determined.

In some examples, as shown in fig. 1 and 2, the system 1 may include a retraction device 20. The retraction device 20 may be connected to a blood pressure treatment device 310. The retraction device 20 may be disposed extracorporeally.

In some examples, as shown in fig. 1, the retracting device 20 may include a driving module 201, a switching module 202, and a signal receiving module 203.

In some examples, the retraction device 20 may be connected to a distal pressure measurement device in the blood pressure processing device 310. For example, the retraction device 20 may be coupled to the blood pressure measuring catheter 110, and the retraction device 20 may have a port that mates with the proximal side 110a of the blood pressure measuring catheter 110. In some examples, the drive module 201 in the retraction device 20 may control the blood pressure measurement catheter 110 to move (e.g., retract) within the blood vessel relative to the guide catheter 100. In some examples, the host 30 may regulate the intravascular withdrawal speed of the blood pressure measuring catheter 110 by controlling the drive module 201.

In some examples, the retraction device 20 may include a switch module 202, and the switch module 202 may be used to control the operating state of the drive module 201. For example, if the switch module 202 is in the on state, the driving module 201 can control the blood pressure measuring tube 110 to automatically retract. If the switch module 202 is in the off state, the drive module 201 is not operated, and manual retraction is enabled, for example, a medical professional may control the retraction of the blood pressure measuring catheter 110 by pulling on the proximal side 110a of the blood pressure measuring catheter 110 or a device connected to the proximal side 110 a.

In some examples, the retraction device 20 may be coupled to the guide catheter 100, and the signal receiving module 203 in the retraction device 20 may receive a first initial pressure signal (e.g., a first pressure signal or a later-described third pressure signal) from the guide catheter 100. In some examples, the retraction device 20 may be connected to the blood pressure measurement catheter 110, and the signal receiving module 203 in the retraction device 20 may receive a second initial pressure signal (e.g., a second pressure signal or a fourth pressure signal described later) from the blood pressure measurement catheter 110.

In some examples, the retraction device 20 may be configured to control the blood pressure measurement catheter 110 to retract and cause the first pressure sensor 102 to measure the pressure within the blood vessel (e.g., the intravascular pressure at the first location) at a second sampling rate to obtain a third pressure signal and the second pressure sensor 112 to measure the pressure within the blood vessel at the second sampling rate to obtain a fourth pressure signal. Thereby, a third pressure signal and a fourth pressure signal can be obtained. In particular, the retraction device 20 may generate a third pressure signal by measuring a pressure within the blood vessel at a second sampling rate at a location proximal to the proximal side 30a (e.g., the first location) during controlled retraction of the blood pressure measurement catheter 110, and the second pressure sensor 112 may generate a fourth pressure signal by measuring a pressure within the blood vessel at a second sampling rate (e.g., a pressure within the blood vessel distal to the proximal side 30a) during retraction of the blood pressure measurement catheter 110.

In some examples, as shown in fig. 1 and 2, system 1 may include a host 30. The host 30 may be connected to the retraction device 20. In some examples, the host 30 may receive pressure signals (e.g., first and second pressure signals, third and fourth pressure signals, etc.) transmitted by the retraction device 20.

In some examples, as shown in fig. 1 and 2, host 30 may include an image processing device 300 and a blood pressure processing device 310. In some examples, the image processing device 300 may be connected with a blood pressure processing device 310. In some examples, the blood pressure treatment device 310 may be connected with the retraction device 20. In some examples, the blood pressure processing device 310 may receive the pressure signal transmitted by the retraction device 20.

In some examples, the blood pressure processing device 310 may control the retraction device 20, for example, whether the retraction device 20 is retracting. In some examples, the host 30 may determine whether the retracting device 20 can retract by itself, determine whether the blood pressure measuring device 10 can stably measure according to the pressure signal received by the host 30, and if the blood pressure measuring device 10 can stably measure, the host 30 may control the retracting device 20 to retract. In some examples, configuring the blood pressure measurement device 10 is done, for example, the blood pressure measurement device 10 may measure the pressure in the blood vessel near the proximal side 30a and the pressure in the blood vessel far from the proximal side 30a and generate pressure signals, and the host 30 may calculate respective variances of the pressure signals based on the received pressure signals to determine whether the blood pressure measurement device 10 can stably measure. However, the examples of the present disclosure are not limited thereto, and in some examples, the pressure signal received by the host 30 may be compared with an electrocardiogram obtained at the same time (for example, whether the electrocardiogram is related to the variation trend of the pressure signal) to determine whether the blood pressure measuring device 10 can stably measure.

In some examples, the image processing apparatus 300 may be an X-ray machine. In some examples, before the blood pressure measuring device 10 is inserted into a blood vessel, a contrast agent may be injected into the patient, an X-ray contrast image of the blood vessel region to be measured may be obtained by the image processing device 300 and a first image signal may be generated and transmitted to the blood pressure processing device 310, and the blood pressure processing device 310 may receive the first image signal and store the first image signal.

In some examples, the X-ray contrast image may include a plurality of coronary arteries, which may be processed sequentially, i.e., the coronary arteries 400 in the X-ray contrast image may be processed one by one, so that the overall lesion status of the blood vessel of the patient may be determined.

In some examples, the position of the image processing device 300 may be kept unchanged, the blood pressure measuring device 10 is inserted into the blood vessel to be measured, and the image processing device 300 may obtain a real-time image of the blood pressure measuring catheter 110 including the developing ring in the blood vessel by X-ray. For example, as the blood pressure measurement catheter 110 is moved (e.g., withdrawn) within the blood vessel, the image processing apparatus 300 may obtain real-time images of the blood pressure measurement catheter 110 including the visualization ring at different locations within the blood vessel via X-rays. In some examples, the image processing device 300 may generate a second image signal from the obtained real-time image and transmit the second image signal to the blood pressure processing device 310.

In some examples, the host 30 may set a withdrawal endpoint according to the X-ray contrast image (i.e., preset a corresponding position in the X-ray contrast image), and the withdrawal device 20 may control the blood pressure measuring catheter 110 to withdraw to the withdrawal endpoint and stop withdrawing. That is, the retracting device 20 can control the blood pressure measuring catheter 110 to be retracted to a preset corresponding position in the X-ray contrast image. Thereby enabling the blood pressure measuring tube 110 to be automatically retracted to the preset corresponding position.

In some examples, the blood pressure processing device 310 may determine whether the blood pressure measuring catheter 110 is retracted to the retraction end point according to the first image signal and the second image signal, and if the blood pressure measuring catheter 110 is retracted to the retraction end point (e.g., the distance between the visualization ring on the blood pressure measuring catheter 110 and the retraction end point is less than or equal to a predetermined distance), the host 30 controls the retraction device 20 to stop the retraction.

In some examples, the withdrawal end point (preset corresponding position) may be selected by the physician at his or her own discretion on the radiographic image. In some examples, the withdrawal end point (preset corresponding position) may correspond to a bifurcation point of a blood vessel or an end of a blood vessel in an X-ray contrast image, for example, the corresponding position may be set to a first position in the X-ray contrast image. Whereby the corresponding position can be determined. In some examples, the withdrawal termination point may be further away from the distal side 30a relative to a location (e.g., the first location) at which the first pressure sensor 102 measures the pressure of the blood vessel, thereby enabling the second pressure sensor 112 to measure the pressure within the blood vessel away from the distal side 30 a.

In some examples, the distal side 100b of the guiding catheter 100 (i.e., the port of the distal side 100 b) may be provided with a visualization ring, the port of the distal side 100b may be used as a withdrawal end point, and the withdrawing device 20 may control the blood pressure measuring catheter 110 to withdraw until the distance between the visualization ring on the blood pressure measuring catheter 110 and the visualization ring on the guiding catheter 100 is equal to or less than a predetermined distance, and the host 30 controls the withdrawing device 20 to stop withdrawing.

In some examples, host computer 30 may calculate the estimated length of the blood vessel based on the width of the visualization ring, the X-ray contrast image, and the real-time image. Specifically, the host computer 30 may obtain the ratio of the width of the development ring in the real-time image to the actual width of the development ring according to the real-time image and the width of the development ring in the length direction of the blood pressure measuring catheter 110, and obtain the ratio of the width of the development ring in the real-time image occupied in the X-ray contrast image of the blood vessel region to be measured according to the real-time image and the X-ray contrast image, thereby being capable of calculating the estimated length of the blood vessel in the X-ray contrast image. For example, the host 30 can calculate the length of the blood pressure measuring catheter 110 to be withdrawn from the initial position (e.g., the second position) to the withdrawal end point (e.g., the first position).

In some examples, the host 30 may control the retraction speed of the retraction device 20 according to the measured length. In other examples, the medical personnel may set the retraction speed of the retraction device 20 by themselves using the host 30. For example, the retracting device 20 is set to retract at a constant speed.

In some examples, the retraction device 20 is configured to control the retraction of the blood pressure measurement catheter 110, and the host 30 can calculate the time of retraction of the blood pressure measurement catheter 110 from the length measured and the speed of retraction. The withdrawal time of the blood pressure measuring catheter 110 can thus be obtained.

In some examples, the host 30 may be connected to the retraction device 20 and receive pressure signals (e.g., first and second pressure signals, third and fourth pressure signals, etc.) transmitted by the retraction device 20.

In some examples, the host 30 may include a blood pressure processing device 310, the blood pressure processing device 310 may include a pre-processing module and a computing module, and the blood pressure processing device 310 may process the received pressure signals.

In some examples, the host 30 may receive a first initial pressure signal and a second initial pressure signal, and the host 30 may obtain the target ratio based on the first initial pressure signal and the second initial pressure signal. In some examples, host 30 may control whether first pressure sensor 102 and second pressure sensor 112 are operational, e.g., collecting pressure signals. In some examples, the host 30 may control whether the retraction device 20 is retracted.

In some examples, when the system 1 is in operation, the blood pressure measuring catheter 110 may be in a static state, the host 30 may control the first pressure sensor 102 and the second pressure sensor 112 to perform pressure measurement within the blood vessel at a sampling rate, the first pressure sensor 102 may measure a pressure within the blood vessel near the proximal side 30a (the first location, e.g., the proximal coronary artery 401) at the first sampling rate and generate a first pressure signal, the second pressure sensor 112 may measure a pressure at a predetermined location within the blood vessel (the second location, e.g., the distal coronary artery 402) at the first sampling rate and generate a second pressure signal, and the first pressure signal and the second pressure signal may be withdrawn from the apparatus 20 and transmitted to the host 30 for processing to obtain a first target ratio. Thereby enabling determination of the presence of a lesion in a blood vessel without injection of a congestion-inducing drug.

In some examples, in operation of the system 1, the retraction device 20 is configured to control the blood pressure measurement catheter 110 to retract and cause the first pressure sensor 102 to measure the intravascular pressure at the second sampling rate and generate a third pressure signal, and the second pressure sensor 112 to measure the intravascular pressure at the second sampling rate and generate a third pressure signal. Specifically, in operation of the system 1, the retraction device 20 is configured to control retraction of the blood pressure measurement catheter 110, the blood pressure measurement catheter 110 is in a retracted state, the guiding catheter 100 is in a resting state, the host computer 30 can control the first pressure sensor 102 and the second pressure sensor 112 to perform pressure measurements within the blood vessel at a sampling rate, the first pressure sensor 102 can measure a pressure within the blood vessel near the proximal side 30a (the first location, e.g., the proximal coronary artery 401) at a second sampling rate and generate a third pressure signal, and the second pressure sensor 112 can measure a pressure within the corresponding blood vessel (e.g., within the blood vessel away from the proximal side 30a) at the second sampling rate and generate a fourth pressure signal during the intravascular retraction. The third pressure signal and the fourth pressure signal may be transmitted to the retracting device 20 and further transmitted to the host 30 for processing to obtain the second target ratio.

In other examples, in operation of the system 1, the retraction device 20 is configured to control the retraction of the blood pressure measurement catheter 110, and the first pressure sensor 102 measures the intravascular pressure at a sample rate and generates a pressure signal that can be transmitted to the retraction device 20 for processing by the host 30.

In some examples, the second pressure sensor 112 and the first pressure sensor 102 may simultaneously measure a third pressure signal and a fourth pressure signal at a second sampling rate. In some examples, the pressure value corresponding to the third pressure signal (third pressure value) and the pressure value corresponding to the fourth pressure signal (fourth pressure value) may correspond one-to-one.

In some examples, the blood pressure processing device 310 includes a pre-processing module that can generate a waveform map based on the pressure signals (e.g., the first and second pressure signals, the third and fourth pressure signals, etc.) received by the host 30, which can be displayed in the form of a waveform, for example, on a display screen. Wherein the vertical axis of the waveform diagram may be the magnitude of the pressure (i.e., the pressure value), and the horizontal axis of the waveform diagram may be the time axis.

In some examples, the pre-processing module may reject signals that are significantly invalid, e.g., a maximum value (or average, peak-to-peak) of the first pressure signal where the maximum value (or average, peak-to-peak) of the second pressure signal is greater than 125%. In some examples, the pre-processing module may automatically synchronize the received pressure signals, e.g., there is a short delay between peaks of the first and second pressure signals, and the pre-processing module may automatically synchronize the first and second pressure signals.

Fig. 5 is a pressure waveform diagram illustrating a plurality of cardiac cycles in accordance with an example of the present disclosure. Fig. 6 is a pressure waveform diagram illustrating one cardiac cycle of fig. 5 in accordance with an example of the present disclosure. Fig. 7 is a pressure waveform diagram illustrating one cardiac cycle of fig. 5 according to another example of the present disclosure.

In some examples, the pressure signals (e.g., the first initial pressure signal and the second initial pressure signal) measured by the blood pressure measurement device 10 may include intravascular pressure of one or more cardiac cycles (see fig. 5).

In some examples, the host 30 may process the received first initial pressure signal and the second initial pressure signal to obtain the target ratio by a pre-configured processing manner. In some examples, the first initial pressure signal received by the host 30 may be a first pressure signal, the second initial pressure signal received by the host 30 may be a second pressure signal, and the host 30 may process the first pressure signal and the second pressure signal to obtain the first target ratio. In some examples, the first initial pressure signal received by the host 30 may be a third pressure signal, the second initial pressure signal received by the host 30 may be a fourth pressure signal, and the host 30 may process the third pressure signal and the fourth pressure signal to obtain a second target ratio.

In some examples, the preprocessing module may obtain a first waveform map including at least one complete cardiac cycle based on a first initial pressure signal (e.g., a first pressure signal) and a second initial pressure signal (e.g., a second pressure signal), the first waveform map including a first variation profile of the first initial pressure signal over time and a second variation profile of the second initial pressure signal over time. Thereby, a first waveform pattern can be obtained. That is, the preprocessing module can obtain a first waveform map based on the first initial pressure signal and the second initial pressure signal, the first waveform map including a first profile and a second profile, the first waveform map can include one or more cardiac cycles. The preprocessing module can obtain a first variation curve of the pressure value (also called "first initial pressure value") corresponding to the first initial pressure signal along with the time based on the first initial pressure signal, and the preprocessing module can obtain a second variation curve of the pressure value corresponding to the second initial pressure signal along with the time based on the second initial pressure signal. For example, as shown in fig. 5, host 30 receives a first initial pressure signal and a second initial pressure signal containing a plurality of consecutive cardiac cycles and may generate a waveform map. In fig. 5, a curve a is a time-varying curve of the first initial pressure signal (i.e., the pressure value corresponding to the first initial pressure signal), and a curve B is a time-varying curve of the second initial pressure signal (i.e., the pressure value corresponding to the second initial pressure signal). A plurality of first initial pressure values and second initial pressure values corresponding to respective first initial pressure values over a plurality of cardiac cycles may be obtained from curve A, B.

In some examples, a method of tracking a cardiac cycle event using blood pressure may include calculating, from a first initial pressure signal and a second initial pressure signal, a ratio of a pressure value of the second initial pressure signal to a pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal to obtain an initial pressure ratio value.

In some examples, the blood pressure processing device 310 includes a calculation module that can further process the waveform map generated by the pre-processing module to obtain a new waveform map.

In some examples, the calculation module may determine a cardiac cycle based on the first waveform map and obtain, based on the first waveform map, a mean of the first initial pressure signal corresponding to the cardiac cycle, an initial pressure ratio of the pressure values of the second initial pressure signal to the pressure values of the first initial pressure signal corresponding to the second initial pressure signal, and a derivative of the second initial pressure signal with respect to time. In particular, the calculation module may determine one or more cardiac cycles included in the first waveform map based on the first waveform map and process the individual cardiac cycles. The calculation module can select any cardiac cycle, obtain a mean value of first initial pressure values and a mean value of second initial pressure values corresponding to the cardiac cycle based on a first variation curve and a second variation curve in the cardiac cycle, and obtain initial pressure ratios of a plurality of second initial pressure values in the cardiac cycle and the first initial pressure values corresponding to the second initial pressure values based on the first variation curve and the second variation curve in the cardiac cycle. The calculation module may also obtain a derivative of the second initial pressure value with respect to time based on the second variation curve.

In some examples, a first intersection point (described in detail later) may be obtained from a mean of pressure values of the first initial pressure signal and the first initial pressure signal. In some examples, the first midpoint time and the second midpoint time (described in detail later) may be obtained from a derivative of the second initial pressure signal with respect to time and the second initial pressure signal.

In some examples, the calculation module may generate a third variation corresponding to a mean of the first initial pressure signal within the cardiac cycle, a fourth variation of the initial pressure ratio value over time within the cardiac cycle, and a fifth variation corresponding to a derivative of the second initial pressure signal in the first waveform map, thereby obtaining a second waveform map including the first variation, the second variation, the third variation, the fourth variation, and the fifth variation. Thereby, a second waveform diagram can be obtained. Specifically, the calculation module may generate a third variation curve in the first waveform map based on the obtained mean value of the first initial pressure values (see curve D in fig. 6), obtain a fourth variation curve of the initial pressure ratio value with time based on the obtained initial pressure ratio values of the plurality of second initial pressure values in the cardiac cycle and the first initial pressure values corresponding to the respective second initial pressure values (see curve C in fig. 6, where curve C shows a pressure ratio value that is a hundred times of the actually calculated pressure ratio value), and obtain a fifth variation curve of the derivative with time based on the obtained derivative of the second initial pressure values with time (see curve E in fig. 7). For example, as shown in fig. 6, a curve a is a curve of a first initial pressure signal (i.e., a pressure value corresponding to the first initial pressure signal) changing with time, a curve B is a curve of a second initial pressure signal (i.e., a pressure value corresponding to the second initial pressure signal) changing with time, a curve C is a curve of a ratio of the second initial pressure value to the first initial pressure value corresponding to each second initial pressure value changing with time, and a curve D is a curve generated by a mean value of the first initial pressure values. As shown in fig. 7, a curve a is a time-varying curve of the first initial pressure signal (i.e., the pressure value corresponding to the first initial pressure signal), a curve B is a time-varying curve of the second initial pressure signal (i.e., the pressure value corresponding to the second initial pressure signal), a curve C is a time-varying curve of the initial pressure ratio of the second initial pressure value to the first initial pressure value corresponding to each second initial pressure value (where the pressure ratio shown by the curve C is a hundred times of the actually calculated pressure ratio), and a curve E is a derivative curve of the second initial pressure value with respect to time (where the ordinate of the curve E corresponds to the value on the right ordinate axis of fig. 7). In some examples, the host 30 may select a desired variation curve according to a specific obtaining manner of a subsequent target ratio (e.g., a first target ratio), and may not obtain all the variation curves (described later). In some examples, the fifth variation curve may be smoothed.

As described above, after the calculation module processes the first waveform diagram, a new variation curve may be generated based on the first waveform diagram, so as to facilitate obtaining the target ratio subsequently.

In some examples, the second waveform map includes feature information, which may include a first intersection point (e.g., point m in fig. 6) of a falling period of the first variation curve and a third variation curve within the selected cardiac cycle (e.g., the selected cardiac cycle may refer to an interval a in fig. 6), that is, the feature information includes a first intersection point, which is an intersection point of the first variation curve and the third variation curve and which is in the falling period of the first variation curve.

In some examples, the characteristic information may include a first midpoint time corresponding to a midpoint of a period from a minimum value of the fifth profile to a maximum value of the second profile within the selected cardiac cycle (see time corresponding to line L1 in fig. 7, i.e., corresponding abscissa axis). In some examples, the characteristic information may include a second midpoint time corresponding to a midpoint of a period from a maximum of the fifth profile to a maximum of the second profile within the selected cardiac cycle (see time corresponding to line L2 in fig. 7). Thereby facilitating subsequent attainment of the target ratio. In some examples, the characteristic information may be determined according to a specific obtaining manner of the subsequent target ratio and the selected variation curve, and all the characteristic information may not be obtained.

In some examples, the blood pressure processing device 310 may process the first initial pressure signal and the second initial pressure signal to obtain the target ratio.

In some examples, the target ratio (e.g., the first target ratio) may be an average of a predetermined number of initial pressure ratios, a minimum of initial pressure ratios corresponding to diastole in the cardiac cycle, a minimum of pressure ratios corresponding to a period (first preset period) in which the first intersection is to the minimum of the first initial pressure signal and the first initial pressure signal is in a continuous decrease, a pressure ratio corresponding to a midpoint of a period (second preset period) in which the first intersection is to the minimum of the first initial pressure signal in the cardiac cycle, an average of pressure ratios corresponding to a period (third preset period) in which the first intersection is to 80% of the cardiac cycle, a first pressure ratio, a second pressure ratio, and a third pressure ratio, which are sequentially selected from small to large from the initial pressure ratios corresponding to the selected cardiac cycle (e.g., the selected cardiac cycle may refer to interval a in fig. 6), An average value of pressure ratios corresponding to a period from the first intersection point to a minimum value of the first initial pressure signal (a second preset period) in the cardiac cycle, a pressure ratio corresponding to a midpoint of a period from the first midpoint time point to the second midpoint time point (a fourth preset period) in the cardiac cycle, or one of averages of pressure ratios corresponding to a period (fifth preset period) from the first occurrence to the last occurrence of the target derivative value in the period (i.e., the fourth preset period) in which the target derivative value appears most frequently in the fifth change curve in the period from the first midpoint time to the second midpoint time in the cardiac cycle (for example, the period may be referred to as a period b in fig. 7) (see a point d in fig. 7, which is a point at which the period b appears most frequently) and in the period (i.e., the fourth preset period) (for example, the period may be referred to as a period c in fig. 7). Thereby, the target ratio can be obtained.

In some examples, host 30 may select one of the above to obtain the target ratio. Thereby determining the pathological condition of the blood vessel to be detected.

In some examples, the method for tracking cardiac cycle events using blood pressure according to the first aspect of the present disclosure may include sequentially selecting a predetermined number of pressure ratio values from the initial pressure ratio values in order of decreasing order to increasing order, and calculating an average value of the predetermined number of pressure ratio values based on the selected predetermined number of pressure ratio values. In some examples, the target ratio value may be an average of a predetermined number of pressure ratio values selected in order of small to large for the corresponding initial pressure ratio value in the selected cardiac cycle. Specifically, the host 30 may process the first initial pressure signal and the second initial pressure signal to obtain a first variation curve, a second variation curve, and further obtain a fourth variation curve, may select any cardiac cycle from the fourth variation curve to process, the host 30 may sequentially select a predetermined number (for example, 3, 4, or 5, etc.) of pressure ratios from small to large from among the pressure ratios corresponding to the cardiac cycle, and the host 30 may calculate an average value of the selected predetermined number of pressure ratios, and take the average value as a target ratio.

In the present disclosure, the pressure within the blood vessel proximal side 30a and the pressure within the blood vessel distal side 30a are measured simultaneously a plurality of times during any one cardiac cycle and first and second initial pressure signals are generated. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. And sequentially selecting a preset number of pressure ratios from the initial pressure ratios in a descending order, and calculating the average value of the preset number of pressure ratios according to the selected preset number of pressure ratios. Thereby, a method of tracking cardiac circulatory events using blood pressure without the need for injection of congestion-inducing drugs can be provided.

In some examples, the method for tracking a cardiac cycle event using blood pressure according to the second aspect of the present disclosure may include calculating a ratio of a pressure value of the second initial pressure signal to a pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal to obtain an initial pressure ratio value according to the first initial pressure signal and the second initial pressure signal. In some examples, the target ratio may be a minimum of the corresponding pressure ratios in the diastolic phase within the selected cardiac cycle. Specifically, the host 30 may process the first initial pressure signal and the second initial pressure signal to obtain a first variation curve, a second variation curve, and further obtain a fourth variation curve, may select any cardiac cycle from the fourth variation curve for processing, and the host 30 may determine a diastolic period of the selected cardiac cycle, select a minimum pressure ratio value from the diastolic period, and may use the minimum pressure ratio value as the target ratio value.

In the present disclosure, the pressure within the blood vessel proximal side 30a and the pressure within the blood vessel distal side 30a are measured simultaneously a plurality of times during any one cardiac cycle and first and second initial pressure signals are generated. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. The pressure ratio values within the diastolic phase of the cardiac cycle are obtained from the initial pressure ratio values, and the smallest pressure ratio value is selected from the pressure ratio values. Thereby, a method of tracking cardiac circulatory events using blood pressure without the need for injection of congestion-inducing drugs can be provided.

In some examples, a method of tracking cardiac cycle events using blood pressure according to the third aspect of the present disclosure may include obtaining pressure ratio values within a first preset period of a cardiac cycle from the initial pressure ratio values, and selecting a minimum pressure ratio value from the pressure ratio values. In some examples, the target ratio may be a minimum pressure ratio over a first predetermined period of the selected cardiac cycle, and the first predetermined period may be a period from a first intersection point to a minimum value of the first initial pressure signal and the first initial pressure signal is at a sustained drop over the selected cardiac cycle. Specifically, the host computer 30 may process the first initial pressure signal and the second initial pressure signal to obtain a first variation curve and a second variation curve, and further obtain a third variation curve and a fourth variation curve, and may select any cardiac cycle from the fourth variation curve to process, and may obtain a first intersection point in the cardiac cycle. The host computer 30 may select a minimum pressure ratio value from the first intersection point to a period of a minimum value of the first initial pressure signal at the sustained falling period, and may use the minimum pressure ratio value as the target ratio value.

In the present disclosure, the pressure within the blood vessel proximal side 30a and the pressure within the blood vessel distal side 30a are measured simultaneously a plurality of times during any one cardiac cycle and first and second initial pressure signals are generated. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. Pressure ratios within a first predetermined period of the cardiac cycle are obtained from the initial pressure ratios and the smallest pressure ratio is selected from the pressure ratios. Thereby, a method of tracking cardiac circulatory events using blood pressure without the need for injection of congestion-inducing drugs can be provided.

In some examples, a method of tracking cardiac cycle events using blood pressure according to a fourth aspect of the present disclosure may include obtaining a pressure ratio value located within a second predetermined period of the cardiac cycle from the initial pressure ratio value, and selecting a pressure ratio value corresponding to a midpoint time of the second predetermined period from the pressure ratio values. In some examples, the target ratio may be a pressure ratio corresponding to a midpoint of a second preset period within the selected cardiac cycle, and the second preset period may be a period from the first intersection to a minimum of the first initial pressure signal within the selected cardiac cycle. Specifically, the host 30 may process the first initial pressure signal and the second initial pressure signal to obtain a first variation curve, a second variation curve, and further obtain a third variation curve and a fourth variation curve, may select any cardiac cycle from the fourth variation curve to process, and may obtain a first intersection point in the selected cardiac cycle. The host 30 may determine a pressure ratio corresponding to a midpoint time of a period from the first intersection point to a minimum value of the first initial pressure value, and may use the pressure ratio as a target ratio.

In the present disclosure, the pressure within the blood vessel proximal side 30a and the pressure within the blood vessel distal side 30a are measured simultaneously a plurality of times during any one cardiac cycle and first and second initial pressure signals are generated. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. A pressure ratio value within a second predetermined period of the cardiac cycle is obtained from the initial pressure ratio values, and a pressure ratio value corresponding to a midpoint time of the second predetermined period is selected from the pressure ratio values. Thereby, a method of tracking cardiac circulatory events using blood pressure without the need for injection of congestion-inducing drugs can be provided.

In some examples, a method of tracking cardiac cycle events using blood pressure as contemplated by the fifth aspect of the present disclosure may include obtaining a pressure ratio value located within a third preset period of the cardiac cycle from the initial pressure ratio values and calculating an average of the pressure ratio values. In some examples, the target ratio may be an average of pressure ratios over a third predetermined period of the selected cardiac cycle, which may be the period from the first intersection to 80% of the selected cardiac cycle. Specifically, the host 30 may process the first initial pressure signal and the second initial pressure signal to obtain a first variation curve, a second variation curve, and further obtain a third variation curve and a fourth variation curve, may select any cardiac cycle from the fourth variation curve to process, and may obtain a first intersection point in the selected cardiac cycle. Host 30 may determine the time corresponding to 80% of the cardiac cycle, and host 30 may average the corresponding pressure ratio values over a period from the first intersection to 80% of the cardiac cycle, and may use the average of the pressure ratio values as the target ratio value.

In the present disclosure, the pressure within the blood vessel proximal side 30a and the pressure within the blood vessel distal side 30a are measured simultaneously a plurality of times during any one cardiac cycle and first and second initial pressure signals are generated. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. A pressure ratio value within a third predetermined period of the cardiac cycle is obtained from the initial pressure ratio values and an average of the pressure ratio values is calculated. Thereby, a method of tracking cardiac circulatory events using blood pressure without the need for injection of congestion-inducing drugs can be provided.

In some examples, a method of tracking cardiac cycle events using blood pressure according to a sixth aspect of the present disclosure may include obtaining pressure ratio values located within a second preset period of a cardiac cycle from the initial pressure ratio values and calculating an average of the pressure ratio values. In some examples, the target ratio may be an average of pressure ratios over a second predetermined period of the selected cardiac cycle, which may be a period from the first midpoint time to the second midpoint time within the selected cardiac cycle. Specifically, the host 30 may process the first initial pressure signal and the second initial pressure signal to obtain a first variation curve, a second variation curve, and further obtain a third variation curve and a fourth variation curve, may select any cardiac cycle from the fourth variation curve to process, and may obtain a first intersection point in the selected cardiac cycle. The host computer 30 may determine an average value of the pressure ratio values in a period from the first intersection point to a minimum value of the first initial pressure value, and take the average value of the pressure ratio values as a target ratio value.

In the present disclosure, the pressure within the blood vessel proximal side 30a and the pressure within the blood vessel distal side 30a are measured simultaneously a plurality of times during any one cardiac cycle and first and second initial pressure signals are generated. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. Pressure ratios within a second predetermined period of the cardiac cycle are obtained from the initial pressure ratios and an average of the pressure ratios is calculated. Thereby, a method of tracking cardiac circulatory events using blood pressure without the need for injection of congestion-inducing drugs can be provided.

In some examples, a method of tracking cardiac cycle events using blood pressure according to a seventh aspect of the present disclosure may include obtaining a pressure ratio value within a fourth preset period of the cardiac cycle from the initial pressure ratio values, and selecting a pressure ratio value corresponding to a midpoint time of the fourth preset period from the pressure ratio values (see point n in fig. 7). In some examples, the target ratio may be a pressure ratio corresponding to a midpoint of a fourth preset time period within the selected cardiac cycle, and the fourth preset time period may be a time period from the first midpoint time instant to the second midpoint time instant within the selected cardiac cycle. Specifically, the host 30 may process the first initial pressure signal and the second initial pressure signal to obtain a first variation curve, a second variation curve, and further obtain a fourth variation curve and a fifth variation curve, may select any cardiac cycle from the fourth variation curve to process, and may obtain a first midpoint time and a second midpoint time within the selected cardiac cycle. The host 30 may determine a midpoint time corresponding to a period from the first midpoint time to the second midpoint time, determine a pressure ratio corresponding to the midpoint time, and may use the pressure ratio as the target ratio.

In the present disclosure, the pressure within the blood vessel proximal side 30a and the pressure within the blood vessel distal side 30a are measured simultaneously a plurality of times during any one cardiac cycle and first and second initial pressure signals are generated. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. And obtaining the pressure ratio value in a fourth preset period of the cardiac cycle from the initial pressure ratio value, and selecting the pressure ratio value corresponding to the midpoint moment of the fourth preset period from the pressure ratio values. Thereby, a method of tracking cardiac circulatory events using blood pressure without the need for injection of congestion-inducing drugs can be provided.

In some examples, a method of tracking cardiac cycle events using blood pressure according to an eighth aspect of the present disclosure may include obtaining a pressure ratio value located within a fifth preset period of a cardiac cycle from the initial pressure ratio values, and calculating an average of the pressure ratio values. In some examples, the target ratio value may be an average of pressure ratio values in a fifth preset period of the selected cardiac cycle, and the fifth preset period may be an average of pressure ratio values corresponding to a period from a first midpoint time to a second midpoint time (a fourth preset period) in the selected cardiac cycle, in which the target derivative value appears most frequently in the fifth variation curve, and a period from a first occurrence to a last occurrence of the target derivative value in the period. Specifically, the host 30 may process the first initial pressure signal and the second initial pressure signal to obtain a first variation curve, a second variation curve, and further obtain a fourth variation curve and a fifth variation curve, may select any cardiac cycle from the fourth variation curve to process, and may obtain a first midpoint time and a second midpoint time within the selected cardiac cycle. The host 30 may select a derivative value with the largest number of occurrences in the fifth variation curve from the first midpoint time to the second midpoint time as the target derivative value, the host 30 may determine a time (i.e., a first time) when the target derivative value first appears and a time (i.e., a second time) when the target derivative value last appears in the period from the first midpoint time to the second midpoint time, the host 30 may obtain an average value of corresponding pressure ratio values in the period from the first time to the second time, and the average value of the pressure ratio values may be used as the target ratio value.

In the present disclosure, the pressure within the blood vessel proximal side 30a and the pressure within the blood vessel distal side 30a are measured simultaneously a plurality of times during any one cardiac cycle and first and second initial pressure signals are generated. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. A pressure ratio value within a fifth preset period of the cardiac cycle is obtained from the initial pressure ratio values, and an average of the pressure ratio values is calculated. Thereby, a method of tracking cardiac circulatory events using blood pressure without the need for injection of congestion-inducing drugs can be provided.

In some examples, if the first initial pressure signal is a first pressure signal and the second initial pressure signal is a second pressure signal, the host 30 may select one of the above to configure the host 30, and may select any cardiac cycle from the waveform diagram, and process the first pressure signal and the second pressure signal corresponding to the cardiac cycle to obtain the first target ratio. In other examples, if the first initial pressure signal is the first pressure signal and the second initial pressure signal is the second pressure signal, the host 30 may also select a plurality of cardiac cycles from the waveform diagram, perform the above processing on each cardiac cycle, obtain a target ratio (herein, the first target ratio) corresponding to each cardiac cycle, and calculate an average value of the target ratios according to the target ratios to obtain a target average value, in which case, the target average value may be used as the first target ratio.

In some examples, the first target ratio may be used as a basis for determining a pathological condition of a blood vessel of the patient, for example, the first target ratio may be compared with a first preset threshold (or range), and the pathological condition of the blood vessel of the patient may be determined by the comparison result. In this case, it is possible to judge the lesion of the blood vessel of the patient more safely and efficiently without the need to inject a congestion-inducing drug. In some examples, the first preset threshold (or range) may be obtained by measuring intravascular pressure of normal persons (i.e., the blood vessel is not diseased).

In the present disclosure, the guiding catheter 100 has a first pressure sensor 102 that acquires a first pressure signal near the proximal side 30a in the blood vessel at a first sampling rate, the blood pressure measuring catheter 110 has a second pressure sensor 112 that acquires a second pressure signal at a preset position at the first sampling rate, and at least one side of the second pressure sensor 112 is provided with a developing ring that is not transmitted with X-rays. The retracting device 20 is connected to the guide catheter 100 and the blood pressure measuring catheter 110 and controls the retracting of the blood pressure measuring catheter 110 in the blood vessel, and the retracting device 20 receives the first pressure signal and the second pressure signal. The host 30 can obtain an X-ray contrast image of the blood vessel and a real-time image of the blood pressure measuring catheter 110 including the developing ring in the blood vessel, calculate a measured length of the blood vessel from the width of the developing ring, the X-ray contrast image and the real-time image, and control a retraction speed of the retraction device based on the measured length, and the host 30 is connected with the retraction device 20 and receives the first pressure signal and the second pressure signal to obtain a first target ratio. In this case, the present disclosure can judge the pathological condition of the blood vessel of the patient without injecting a congestion-inducing drug.

In some examples, if the first initial pressure signal is a third pressure signal and the second initial pressure signal is a fourth pressure signal, the host 30 may select one of the above to configure the host 30, and the host 30 may select a plurality of cardiac cycles from the corresponding waveform map to process, and perform the above processing on each cardiac cycle, so as to obtain a second target ratio corresponding to each cardiac cycle. However, examples of the present disclosure are not limited thereto, and in some examples, the host 30 may calculate a ratio of each fourth pressure value to a third pressure value corresponding to each fourth pressure value according to the third pressure signal and the fourth pressure signal to obtain a plurality of second target ratios. In other examples, in operation of the system 1, the retraction device 20 is configured to control retraction of the blood pressure measuring catheter 110, and the first pressure sensor 102 obtains the intravascular pressure distal to the proximal side 30a at a sampling rate and generates a pressure signal that may be transmitted to the retraction device 102 for processing by the host computer 30 (described below), wherein the first pressure sensor may be without limitation.

In some examples, host 30 may determine, according to the obtained plurality of second target ratios, the first image signal and the second image signal, a target position in the blood vessel corresponding to each of the second target ratios. Specifically, the blood pressure processing device 310 may determine a time corresponding to each of the second target ratios according to the obtained plurality of second target ratios, and then determine a target position at which the second pressure sensor 112 is located at the time using the first image signal and the second image signal, and the blood pressure processing device 310 may mark the second target ratio at the target position. The blood pressure processing apparatus 310 may display the X-ray contrast images marked with the plurality of second target ratios in the image processing apparatus 300 (see the image processing apparatus 300 in fig. 2). In some examples, the second target ratio may be used as a basis for determining a lesion condition of a blood vessel of the patient, and based on a comparison result between the second target ratio at each target position on the image and the first preset threshold (or range), a lesion region of the blood vessel may be determined more specifically, so that a size of a region to be implanted with the stent may be determined more specifically.

Examples of the present disclosure are not so limited, and in some examples, the retraction device 20 is configured to control retraction of the blood pressure measurement catheter 110 and the second pressure sensor 112 may measure pressure within the blood vessel distal the proximal side 30a and generate a third pressure signal that the host 30 may receive while the system 1 is in operation. The host 30 may determine each cardiac cycle included in the third pressure signal according to the third pressure signal, further determine a corresponding pressure value at a diastolic end of each cardiac cycle, and determine a corresponding position of each pressure value in the X-ray contrast image based on the X-ray contrast image and the real-time image, further determine a specific lesion condition of a blood vessel of the patient according to the pressure values corresponding to a plurality of positions in the X-ray contrast image, and further more specifically determine a size of a portion to be implanted with the stent.

In other examples, in operation of the system 1, the retraction device 20 is configured to control retraction of the blood pressure measuring catheter 110, and the second pressure sensor 112 may measure the pressure within the blood vessel distal the proximal side 30a and generate a third pressure signal, and the external instrument may simultaneously obtain an electrocardiogram of the patient and the host 30 may receive the third pressure signal. The corresponding pressure value of the end of the diastolic period of each cardiac cycle in the third pressure signal can be determined according to the electrocardiogram and the third pressure signal, the host 30 determines the corresponding position of each pressure value in the X-ray contrast image based on the X-ray contrast image and the real-time image, and further determines the specific pathological change condition of the blood vessel of the patient according to the pressure values corresponding to a plurality of positions in the X-ray contrast image, and further determines the size of the part to be implanted with the stent more specifically.

In some examples, the blood pressure measuring device 10 may be used to measure the pressure of each coronary artery in the X-ray contrast image and the host computer 30 may be used to process the pressure measurement, so that the specific lesion of each coronary artery may be determined.

While the present disclosure has been described in detail in connection with the drawings and examples, it should be understood that the above description is not intended to limit the disclosure in any way. Those skilled in the art can make modifications and variations to the present disclosure as needed without departing from the true spirit and scope of the disclosure, which fall within the scope of the disclosure.

Claims

1. A method of tracking cardiac cycle events using blood pressure,

the method comprises the following steps:

measuring the pressure in the blood vessel close to the near end side at a certain sampling rate in any cardiac cycle and generating a first initial pressure signal, and measuring the pressure in the blood vessel far from the near end side at a certain sampling rate and generating a second initial pressure signal;

according to the first initial pressure signal and the second initial pressure signal, calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal to obtain an initial pressure ratio, and

and sequentially selecting a preset number of pressure ratios from the initial pressure ratios in a descending order, and calculating the average value of the preset number of pressure ratios according to the selected preset number of pressure ratios.

2. The method of claim 1, wherein:

the cardiac cycle includes the entire cycle of diastole and systole.

3. A method of tracking cardiac cycle events using blood pressure,

the method comprises the following steps:

measuring the pressure in the blood vessel close to the proximal side at a certain sampling rate and generating a first initial pressure signal, and measuring the pressure in the blood vessel far from the proximal side at a certain sampling rate and generating a second initial pressure signal in any one cardiac cycle, wherein the cardiac cycle comprises the diastole period of diastole and the systole period of systole;

obtaining pressure ratios within the diastolic phase of the cardiac cycle from the initial pressure ratios, and selecting a minimum pressure ratio from the pressure ratios.

4. A method of tracking cardiac cycle events using blood pressure,

the method comprises the following steps:

obtaining pressure ratio values within a first preset period of the cardiac cycle from the initial pressure ratio values, and selecting a minimum pressure ratio value from the pressure ratio values,

the method comprises the steps of obtaining a mean value of pressure values of a first initial pressure signal according to the first initial pressure signal, obtaining a first intersection point according to the first initial pressure signal and the mean value, and enabling a first preset period to be a period from the first intersection point to the minimum value of the first initial pressure signal and enabling the first initial pressure signal to be in continuous descending.

5. A method of tracking cardiac cycle events using blood pressure,

the method comprises the following steps:

obtaining the pressure ratio value in a second preset period of the cardiac cycle from the initial pressure ratio value, and selecting the pressure ratio value corresponding to the midpoint moment of the second preset period from the pressure ratio values,

and obtaining a mean value of the pressure values of the first initial pressure signal according to the first initial pressure signal, obtaining a first intersection point according to the first initial pressure signal and the mean value, wherein the second preset period is a period from the first intersection point to a minimum value of the first initial pressure signal.

6. A method of tracking cardiac cycle events using blood pressure,

the method comprises the following steps:

obtaining a pressure ratio value within a third preset period of the cardiac cycle from the initial pressure ratio values and calculating an average of the pressure ratio values,

wherein a mean value of the pressure values of the first initial pressure signal is obtained from the first initial pressure signal, a first intersection point is obtained from the first initial pressure signal and the mean value, and the third preset period is a period from the first intersection point to 80% of the cardiac cycle.

7. A method of tracking cardiac cycle events using blood pressure,

the method comprises the following steps:

obtaining pressure ratio values within a second preset period of the cardiac cycle from the initial pressure ratio values and calculating an average of the pressure ratio values,

8. A method of tracking cardiac cycle events using blood pressure,

the method comprises the following steps:

obtaining a pressure ratio value in a fourth preset period of the cardiac cycle from the initial pressure ratio value, and selecting a pressure ratio value corresponding to the midpoint moment of the fourth preset period from the pressure ratio values,

and obtaining a derivative of the second initial pressure signal with respect to time according to the second initial pressure signal, obtaining a first midpoint time and a second midpoint time according to the second initial pressure signal and the derivative, and setting the fourth preset period as a period from the first midpoint time to the second midpoint time.

9. A method of tracking cardiac cycle events using blood pressure,

the method comprises the following steps:

obtaining a pressure ratio value within a fifth preset period of the cardiac cycle from the initial pressure ratio values and calculating an average of the pressure ratio values,

the fifth preset period is a target derivative value in which the derivative value of the second pressure signal with respect to time appears most frequently in the fourth preset period and a period from first occurrence to last occurrence of the target derivative value in the fourth preset period, a derivative of the second initial pressure signal with respect to time is obtained according to the second initial pressure signal, a first midpoint moment and a second midpoint moment are obtained according to the second initial pressure signal and the derivative, and the fourth preset period is a period from the first midpoint moment to the second midpoint moment.